Common approach for compensation of axial motion artifacts in swept-source OCT and dispersion in Fourier-domain OCT

Optical coherence tomography (OCT) has become an important imaging modality with numerous biomedical applications. Challenges in high-speed, high-resolution, volumetric OCT imaging include managing dispersion, the trade-off between transverse resolution and depth-of-field, and correcting optical aberrations that are present in both the system and sample. Physics-based computational imaging techniques have proven to provide solutions to these limitations. This review aims to outline these computational imaging techniques within a general mathematical framework, summarize the historical progress, highlight the state-of-the-art achievements, and discuss the present challenges. Swanson, "Optical biopsy and imaging using optical coherence tomography," Nat. Med. 1(9), 970-972 (1995). 3. G. J. Tearney, M. E. Brezinski, B. E. Bouma, S. A. Boppart, C. Pitris, J. F. Southern, and J. G. Fujimoto, "In vivo endoscopic optical biopsy with optical coherence tomography," Science 276(5321), 2037-2039 (1997). 4. S. A. Boppart, B. E. Bouma, C. Pitris, J. F. Southern, M. E. Brezinski, and J. G. Fujimoto, "In vivo cellular optical coherence tomography imaging," Nat. Med. 4(7), 861-865 (1998). Sundaram, P. S. Ray, and S. A. Boppart, "Real-time imaging of the resection bed using a handheld probe to reduce incidence of microscopic positive margins in cancer surgery," Cancer Res. 75(18), 3706-3712 (2015). 9. J. G. Fujimoto and E. A. Swanson, "The development, commercialization, and impact of optical coherence tomography," Invest. Ophthalmol. Vis. Sci. 57(9), OCT1-OCT13 (2016). 10. A. M. Cormack, "Representation of a function by its line integrals, with some radiological applications. II," J.Appl. Phys. 35(10), 2722-2727 (1964). 11. G. N. Hounsfield, "Computerized transverse axial scanning (tomography). 1. Description of system," Br. J.Radiol. 46(552), 1016-1022 (1973). 12. P. C. Lauterbur, "Image formation by induced local interactions: examples employing nuclear magnetic resonance," Nature 242(5394), 190-191 (1973). 13. P. T. Gough and D. W. Hawkins, "Unified framework for modern synthetic aperture imaging algorithms," Int. J.Imaging Syst. Technol. 8(4), 343-358 (1997). shaping for optimal depth-selective focusing in optical coherence tomography," Opt. Express 21(3), 2890-2902 (2013 111-115 (1962). 77. L. Cutrona, E. Leith, C. Palermo, and L. Porcello, "Optical data processing and filtering systems," IRE Trans.Inf. Theory 6(3), 386-400 (1960). 78. L. J. Cutrona, E. N. Leith, L. J. Porcello, and E. W. Vivian, "On the application of coherent optical processing techniques to synthetic-aperture radar," Proc. IEEE 54(8), 1026-1032 (1966). 79. W. Brown and L. Porcello, "An introduction to synthetic-aperture radar," IEEE Spectr. 6(9), 52-62 (1969). 80. M. P. Hayes and P. T. Gough, "Broad-band synthetic aperture sonar," IEEE J. Oceanic Eng. 17(1), 80-94 (1992)

Section: Post-processing Methods For Phase Stabilizationmentioning

confidence: 99%

Computational optical coherence tomography [Invited]

Liu

South

et al. 2017

“…While line-and full-field OCT can generate very high effective line rates, the acquisition time for a single-line or volume is relatively long. Hence, they are much more prone to motion artifacts as very slow OCT systems, although numerical correction schemes exist [163]. Streak mode OCT also uses a 2D camera, but maintains confocal scanning by recording the spectrum in streak mode, demonstrated at up to 2 MHz [164].…”

Section: Line-field and Full-field Octmentioning

confidence: 99%

High-speed OCT light sources and systems [Invited]

Klein¹,

Huber²

2017

201

111

Abstract:Imaging speed is one of the most important parameters that define the performance of optical coherence tomography (OCT) systems. During the last two decades, OCT speed has increased by over three orders of magnitude. New developments in wavelength-swept lasers have repeatedly been crucial for this development. In this review, we discuss the historical evolution and current state of the art of high-speed OCT systems, with focus on wavelength swept light sources and swept source OCT systems. 3067-3086 (2012). 7. J. Xu, X. Wei, L. Yu, C. Zhang, J. Xu, K. K. Y. Wong, and K. K. Tsia, "High-performance multi-megahertz optical coherence tomography based on amplified optical time-stretch," Biomed. Opt. Express 6(4), 1340-1350 (2015). 8. D. J. Fechtig, B. Grajciar, T. Schmoll, C. Blatter, R. M. Werkmeister, W. Drexler, and R. A. Leitgeb, "Line-field parallel swept source MHz OCT for structural and functional retinal imaging," Biomed. Opt. Express 6(3), 716-735 (2015). 9. T. Klein, W. Wieser, L. Reznicek, A. Neubauer, A. Kampik, and R. Huber, "Multi-MHz retinal OCT," Biomed.Opt. Express 4(10), 1890-1908 (2013). 10. E. A. Swanson, D. Huang, M. R. Hee, J. G. Fujimoto, C. P. Lin, and C. A. Puliafito, "High-speed optical coherence domain reflectometry," Opt. Lett. 17(2), 151-153 (1992). 11. G. J. Tearney, B. E. Bouma, S. A. Boppart, B. Golubovic, E. A. Swanson, and J. G. Fujimoto, "Rapid acquisition of in vivo biological images by use of optical coherence tomography," Opt. Lett. 21(17), 1408-1410 (1996). 12. G. J. Tearney, B. E. Bouma, and J. G. Fujimoto, "High-speed phase-and group-delay scanning with a gratingbased phase control delay line," Opt. Lett. 22(23), 1811-1813 (1997). 13. A. Rollins, S. Yazdanfar, M. Kulkarni, R. Ung-Arunyawee, and J. Izatt, "In vivo video rate optical coherence tomography," Opt. Express 3(6), 219-229 (1998). 14. G. Häusler and M. W. Lindner, "Coherence radar and 'spectral radar'-new tools for dermatological diagnosis," J.Biomed. Opt. 3(1), 21-31 (1998). 15. B. Golubovic, B. E. Bouma, G. J. Tearney, and J. G. Fujimoto, "Optical frequency-domain reflectometry using rapid wavelength tuning of a Cr4+:forsterite laser," Opt. Lett. 22(22), 1704-1706 (1997). 16. S. R. Chinn, E. A. Swanson, and J. G. Fujimoto, "Optical coherence tomography using a frequency-tunable optical source," Opt. Lett. 22(5), 340-342 (1997). 17. M. Wojtkowski, R. Leitgeb, A. Kowalczyk, T. Bajraszewski, and A. F. Fercher, "In vivo human retinal imaging by Fourier domain optical coherence tomography," J. Biomed. Opt. 7(3), 457-463 (2002). 18. L. Kranendonk, R. Bartula, and S. Sanders, "Modeless operation of a wavelength-agile laser by high-speed cavity length changes," Opt. Express 13(5), 1498-1507 (2005). 656-664 (2012). 36. C. Henry, "Theory of the linewidth of semiconductor lasers," IEEE J. Quantum Electron. 18(2), 259-264 (1982). 37. J. Geng, Q. Wang, J. Wang, S. Jiang, and K. Hsu, "All-fiber wavelength-swept laser near 2 μm," Opt. Lett. 3771-3773 (2011). 38. F. Nielsen, L. Thrane, J. Black, A. Bjarklev, and P. Ander...

“…Motion that occurs during the acquisition of the volume causes characteristic artifacts in the reconstructed volume, which are equivalent to group velocity dispersion (GVD) mismatch between reference and sample arm [24]. For example, acquisition of a single depth profile with an axial motion described by constant velocity v that moves over a depth ∆z during the entire sweep results in the following modified cross-correlation term as a function of the time t:…”

Section: Axial Phase Errors In Parallelized Fd-octmentioning

confidence: 99%

“…However, since those calibration measurements have to be implemented on a specific fixed sample, e.g., a mirror, they only detect the phase error caused by the setup and are therefore not suited for compensating artifacts caused by sample motion. To overcome this problem other algorithms were developed [24][25][26], e.g., based on short-time Fourier transforms or the optimization of image quality. Improvements in image quality vary.…”

Section: Axial Phase Errors In Parallelized Fd-octmentioning

confidence: 99%

Reduction of frame rate in full-field swept-source optical coherence tomography by numerical motion correction [Invited]

Pfäffle

Spahr

Hillmann

et al. 2017

Self Cite

Full-field swept-source optical coherence tomography (FF-SS-OCT) was recently shown to allow new and exciting applications for imaging the human eye that were previously not possible using current scanning OCT systems. However, especially when using cameras that do not acquire data with hundreds of kHz frame rate, uncorrected phase errors due to axial motion of the eye lead to a drastic loss in image quality of the reconstructed volumes. Here we first give a short overview of recent advances in techniques and applications of parallelized OCT and finally present an iterative and statistical algorithm that estimates and corrects motion-induced phase errors in the FF-SS-OCT data. The presented algorithm is in many aspects adopted from the phase gradient autofocus (PGA) method, which is frequently used in synthetic aperture radar (SAR). Following this approach, the available phase errors can be estimated based on the image information that remains in the data, and no parametrization with few degrees of freedom is required. Consequently, the algorithm is capable of compensating even strong motion artifacts. Efficacy of the algorithm was tested on simulated data with motion containing varying frequency components. We show that even in strongly blurred data, the actual image information remains intact, and the algorithm can identify the phase error and correct it. Furthermore, we use the algorithm to compensate real phase error in FF-SS-OCT imaging of the human retina. Acquisition rates can be reduced by a factor of three (from 60 to 20 kHz frame rate) with an image quality that is even higher compared to uncorrected volumes recorded at the maximum acquisition rate. The presented algorithm for axial motion correction decreases the high requirements on the camera frame rate and thus brings FF-SS-OCT closer to clinical applications.